KR102511907B1 - Non-invasive biomaterial sugar concentration measurement system and method using optical module - Google Patents

Abstract

Disclosed are a system and method for non-invasively measuring sugar concentration in a biomaterial using an optical module. A non-invasive biomaterial sugar concentration measurement system using an optical module according to an embodiment includes a diffraction grating for outputting light for each wavelength using parallel light input from a sample; a second lens that reflects the output light for each wavelength to a mirror and then selects light of a specific desired wavelength from among the light for each wavelength; and a detector for detecting an optical signal of the light of the selected specific wavelength.

Description

Non-invasive biomaterial sugar concentration measurement system and method using an optical module

The present invention relates to a system and method for non-invasively measuring the sugar concentration of biomaterials using an optical module, which includes spectroscopy, industrial biotechnology, bioanalysis equipment, biomaterial analysis, data analysis, and optical measurement as related fields.

This task (outcome) is the result of a regional innovation project based on local government-university cooperation conducted with the support of the National Research Foundation of Korea (Task number: 2020 University Innovation-147) funded by the Ministry of Education in 2020 (This results was supported by " Regional Innovation Strategy (RIS)" through the National Research Foundation of Korea (NRF) funded by the Ministry of Education (MOE))

Sugar is an important component in biological activities such as plant growth, animal energy supply, brain activation, stress relief, and fatigue recovery.

Sugar is a common method for measuring sugar by extracting liquid components of animals/plants, but a non-invasive method capable of measuring sugar without damaging the living body is required.

Diabetes is the 6th leading cause of death in Korea and is classified into endocrine, nutritional and metabolic diseases. There are more than 350 million diabetic patients worldwide, and the number is expected to increase rapidly due to aging.

A diabetic patient needs to draw blood six or more times a day, and suffers from severe physical and mental pain due to the pain of drawing blood.

Accordingly, in recent years, there has been a demand for the development of a non-invasive/bloodless blood glucose measurement technology that can be conveniently used.

However, existing non-invasive blood glucose measurement methods have limitations.

As for the existing non-invasive blood glucose measurement methods, studies on small planar resonators or radiators that can contact the human body have been reported as part of attempts to measure blood sugar using a non-invasive method. It is becoming.

However, most of the microwave signals radiated from the planar resonator are reflected near the skin or subcutaneous tissue, resulting in limited sensitivity improvement.

In addition, among the existing non-invasive blood glucose measurement methods, in the case of the reverse iontophoresis method, the glucose pad in contact with the skin must be replaced every 12 hours, and there is a disadvantage in that preparation time and readjustment process are required for each replacement. .

In addition, among existing non-invasive blood glucose measurement methods, in the case of impedance spectroscopy, since it changes according to body position, temperature, skin perspiration, or micro blood flow, correction thereof is necessarily required.

In addition, among existing non-invasive blood glucose measurement methods, in the case of a lens type, there is a risk of low-temperature burns due to heat emitted from a circuit.

In addition, among existing non-invasive blood glucose measurement methods, in the case of the polarization method, the plane of polarization of light is rotated at a specific angle when passing through a solution containing sugar, and the degree of rotation is affected by temperature or pH. A disadvantage is that specificity for sugar is lowered when an optically active substance such as ascorbate or albumin is present in the tissue.

In addition, among the existing non-invasive blood glucose measurement methods, the fluorescence method uses the property that tissue generates fluorescence when light of a specific frequency is received. The intensity of fluorescence is determined by the sugar concentration in the solution, but the sugar concentration must be high There are downsides to being measurable.

Therefore, there is an urgent need for a blood glucose measurement method through reflectance spectroscopy, biosignal measurement, light-biological tissue interaction, and blood sampling.

As related prior art, Korean Publication No. 10-2008-0026159 (Apparatus and method for non-invasive sensing of glucose in human subjects), US Registration No. US 6,424,8489 METHOD FOR PREPARING SKIN SURFACE AND DETERMINING GLUCOSE LEVELS FROM THAT SURFACE), and Korean Registration No. 10-1939956 (A method for analyzing the nanostructure of a myelinated nerve axon using reflection spectroscopy).

An embodiment of the present invention uses an optical module to measure the sugar component concentration of a biological material by a non-invasive optical technique, increase measurement accuracy based on quantified data, and build a user-friendly system that can be used by the general public. An object to be solved is to provide a non-invasive biomaterial sugar concentration measuring system and method.

However, the technical challenges are not limited to the above-described technical challenges, and other technical challenges may exist.

A non-invasive biomaterial sugar concentration measurement system using an optical module according to an embodiment includes a diffraction grating that outputs light for each wavelength using parallel light input from a sample; a second lens that reflects the output light for each wavelength to a mirror and then selects light of a specific desired wavelength from among the light for each wavelength; and a detector for detecting an optical signal of the selected specific wavelength of light.

A non-invasive biomaterial sugar concentration measurement system using an optical module accumulates and stores the detected optical signal for a predetermined period of time, and uses the accumulated optical signal to store an optical signal associated with the sample according to the sugar concentration. It may further include a handler that builds a graph of changes.

The processor may determine a sensitive region of the optical signal in the graph of optical signal change according to the sugar concentration, and mark a window in an amplitude range corresponding to the determined sensitive region.

The processor builds a graph showing a correlation between the sugar concentration and the light signal as a graph of light signal change according to the sugar concentration, and the graph showing the correlation is the higher the sugar concentration, the higher the absorbance ( Abs) may be a graph in which gradually and gently increases.

A non-invasive biological material sugar concentration measurement system using an optical module includes a light source generating light energy and departing from the sample; and a first lens configured to convert the reflected light into the collimated light as the light energy reflected by the sample is diffused and converted into reflected light while passing through the slit, wherein the diffraction grating converts the collimated light into a wavelength It is possible to output light for each wavelength by dispersing according to the wavelength.

A method for non-invasively measuring the sugar concentration of a biomaterial using an optical module includes outputting light for each wavelength using parallel light input from a sample in a diffraction grating; In a second lens, after reflecting the output light for each wavelength to a mirror, selecting light of a specific target wavelength from among the light for each wavelength; and detecting, in a detector, an optical signal of the selected specific wavelength of light.

A non-invasive method for measuring the sugar concentration of a biomaterial using an optical module includes accumulating and storing the detected optical signal for a predetermined period in a processor; and constructing, in the processor, a graph of an optical signal change according to a sugar concentration associated with the sample using the accumulated and stored optical signals.

A non-invasive method for measuring the sugar concentration of a biomaterial using an optical module includes determining, in the processor, a sensitive region of an optical signal in a graph of optical signal change according to the sugar concentration; and marking a window in an amplitude range corresponding to the determined sensitive region in the processor.

The non-invasive method for measuring the sugar concentration of a biological material using an optical module further comprises constructing, in the processor, a graph representing a correlation between the sugar concentration and the optical signal as a graph of light signal change according to the sugar concentration. And, the graph showing the correlation may be a graph in which the absorbance (Abs) gradually increases as the sugar concentration increases.

A non-invasive biomaterial sugar concentration measurement method using an optical module includes generating light energy from a light source and starting the sample; and converting the reflected light into the collimated light as the light energy reflected by the sample is diffused and converted into reflected light while passing through the slit in the first lens, and outputting light for each wavelength. The may include dispersing the collimated light according to wavelengths and outputting light for each wavelength.

1 is a block diagram showing the configuration of a non-invasive biomaterial sugar concentration measurement system using an optical module according to an embodiment of the present invention.
2 is a diagram for explaining the characteristics of specular reflection and diffuse reflection.
3 is a diagram for comparison between a transmission type measurement method and a reflection type measurement method.
4 is a diagram explaining the structure of a non-invasive biomaterial sugar concentration measurement system according to the present invention.
5 is a diagram showing a relationship between an optical signal Abs and a wavelength according to the present invention.
6 is an example of a graph of an optical signal corresponding to a sugar concentration at a highly sensitive wavelength according to the present invention.
7 is a flowchart illustrating a method for non-invasively measuring a sugar concentration of a biological material using an optical module according to an embodiment of the present invention.

Specific structural or functional descriptions of the embodiments are disclosed for illustrative purposes only, and may be changed and implemented in various forms. Therefore, the form actually implemented is not limited only to the specific embodiments disclosed, and the scope of the present specification includes changes, equivalents, or substitutes included in the technical idea described in the embodiments.

Although terms such as first or second may be used to describe various components, such terms should only be construed for the purpose of distinguishing one component from another. For example, a first element may be termed a second element, and similarly, a second element may be termed a first element.

It should be understood that when an element is referred to as being “connected” to another element, it may be directly connected or connected to the other element, but other elements may exist in the middle.

Singular expressions include plural expressions unless the context clearly dictates otherwise. In this specification, terms such as "comprise" or "have" are intended to designate that the described feature, number, step, operation, component, part, or combination thereof exists, but one or more other features or numbers, It should be understood that the presence or addition of steps, operations, components, parts, or combinations thereof is not precluded.

Unless defined otherwise, all terms used herein, including technical or scientific terms, have the same meaning as commonly understood by one of ordinary skill in the art. Terms such as those defined in commonly used dictionaries should be interpreted as having a meaning consistent with the meaning in the context of the related art, and unless explicitly defined in this specification, it should not be interpreted in an ideal or excessively formal meaning. don't

Hereinafter, embodiments will be described in detail with reference to the accompanying drawings. In the description with reference to the accompanying drawings, the same reference numerals are given to the same components regardless of reference numerals, and overlapping descriptions thereof will be omitted.

1 is a block diagram showing the configuration of a non-invasive biomaterial sugar concentration measurement system using an optical module according to an embodiment of the present invention.

Referring to FIG. 1, a non-invasive biological material sugar concentration measuring system (hereinafter referred to as 'non-invasive biological material sugar concentration measuring system', 100) using an optical module according to an embodiment of the present invention includes a light source 110 ), a first lens 120, a diffraction grating 130, a second lens 140, a detector 150, and a processor 160.

First, the light source 110 generates light energy and sends it to the sample. That is, the light source 110, as an object or device that emits light, may play a role of emitting light and outputting it in the form of energy (light energy) as a sample.

The sample is an object for measuring sugar concentration, and may be the skin of a patient whose sugar concentration is measured through conventional blood sampling.

The first lens 120 converts the reflected light into collimated light as the light energy reflected by the sample is diffused and converted into reflected light while passing through the slit. That is, the first lens 120 may serve to convert the diffuse reflected light converted by the sample and the slit into collimated light.

A slit may be a means of diffusing light through a small hole.

The first lens 120 may be a parallel lens that parallelizes the propagation direction of the light diffused through the slit.

The diffraction grating 130 outputs light for each wavelength using parallel light input from the sample. That is, the diffraction grating 130 may serve to spread the parallel light by dispersing the wavelength unit.

The diffraction grating 130 is a device that separates the spectrum of light according to the wavelength by using the diffraction phenomenon of light, and obtains the spectrum by dividing the parallel light passing through the slit according to the wavelength, thereby outputting the light according to the wavelength.

The second lens 140 reflects the output light for each wavelength to a mirror, and then selects light of a specific desired wavelength from among the light for each wavelength. That is, the second lens 140 may serve to pass only light of a specific wavelength that is reflected in a predetermined direction by the mirror and passes therethrough.

The mirror may have a structure that changes the propagation direction of light for a desired wavelength differently from that of other wavelengths.

The second lens 140 may be a filter parallel lens that passes light of a specific wavelength that is reflected by a mirror and reflected in a predetermined traveling direction.

The detector 150 detects an optical signal of the selected specific wavelength of light. That is, the detector 150 may serve to sense light of a specific wavelength selected by the second lens 140 .

The detector 150 may be designed to repeatedly detect only light of a specific wavelength.

The processor 160 accumulates and stores the sensed light signal for a predetermined period of time, and builds a graph of light signal change according to sugar concentration associated with the sample using the accumulated light signal. That is, the processor 160 may play a role of accumulating the optical signals detected by the detector 150 according to the arrival of the cycle and visualizing the optical signal change for the sample in a graph using the accumulated optical signals.

The processor 160 may determine a sensitive region of the optical signal in the graph of optical signal change according to the sugar concentration, and mark a window in an amplitude range corresponding to the determined sensitive region.

For example, the processor 160 marks a window with an amplitude region in which the optical signal change is relatively large (e.g., about 580 to 620 nm in FIG. Signal sensitive areas can be divided and displayed.

Also, the processor 160 may construct a graph representing a correlation between the sugar concentration and the optical signal as a graph of light signal change according to the sugar concentration.

For example, as a graph representing the correlation, the processor 160 may build a graph in which the absorbance (Abs) gradually increases as the sugar concentration increases. The graph is a logarithmic function as shown in FIG. 6 It may have the form of, and depending on conditions, it may be a polynomial function, an exponential function, or the like.

According to the present invention, a non-invasive optical technique measures the sugar component concentration of a biological material, increases measurement accuracy based on quantified data, and builds a user-friendly system that can be used by the general public. It is possible to provide an invasive biomaterial sugar concentration measurement system and method.

2 is a diagram for explaining the characteristics of specular reflection and diffuse reflection.

The non-invasive biological material sugar concentration measurement system 100 of the present invention can conduct concentration measurement application research of diffuse reflection optical signals as a theoretical background and principle.

Reflection of light can be divided into specular reflection occurring on the surface of the medium and diffuse reflection derived as a result of absorption and scattering inside the medium.

Specular reflection is reflection that obeys the law of reflection in a macroscopic view on a diffuse-type reflective surface, and is also called regular reflection.

Diffuse reflection may refer to physical light, sound, and radio waves being reflected while being scattered in all directions from the surface of an object according to the cosine law.

Specular reflection and diffuse reflection can be used to measure sugar concentration by analyzing signals that interact with biomaterials as the path of light changes.

3 is a diagram for comparison between a transmission type measurement method and a reflection type measurement method.

The transmission type measurement method is affected by the sample thickness, but the reflection type measurement method has the advantage of obtaining a constant optical signal even if the thickness is different because it can be regarded as a semi-infinite medium if the thickness is greater than a certain thickness.

In addition, the transmission type measurement method requires consideration of the sample thickness, but the reflection type measurement method does not require consideration of the sample thickness.

The transmission type measurement method is used to measure optical communication loss, and may be a method of directly measuring the amount of attenuation of optical power passing through an optical fiber. The transmission measurement method can be expressed as "α [dB] = 10 log ( Pin / Pout )", which is the ratio of the optical power at the entrance end of the optical fiber to the optical power at the exit end. The transmission type measurement method may be a total loss characteristic measurement method of a unit section or entire section of an optical line.

The reflection measurement method is a method of evaluating the loss characteristics of an optical fiber by using a phenomenon in which a part of the light propagating in the optical fiber is returned to the incident end side by Fresnel reflecter and Rayleigh scattering. called the law

4 is a diagram explaining the structure of a non-invasive biomaterial sugar concentration measurement system according to the present invention.

As shown in FIG. 4, the non-invasive biomaterial sugar concentration measuring system 100 includes a light source 2, a first lens 4, a diffraction grating 5, a mirror 6, and a second lens. (7), it can be configured to include a detector (8).

The light source 2 generates light energy and launches it into the sample 1 .

The emitted light energy is reflected by the sample 1 and passes through the slit 3.

The reflected light diffused while passing through the slit 3 is converted into parallel light by the first lens 4 .

The diffraction grating 5 disperses the parallel light according to the wavelength and outputs it to the mirror 6. Light for each wavelength output from the diffraction grating 5 is diffused by a lens and reaches the mirror 6 .

The mirror 6 reflects the light for each wavelength reached.

The second lens 7 selects light of a specific target wavelength from the light reflected from the mirror 6 for each wavelength.

The detector 8 detects an optical signal of light of a specific wavelength selected by the second lens 7 .

The PC 9 accumulates and stores the optical signals sensed by the detector 8, and builds a graph of the optical signal change according to the sugar concentration.

5 is a diagram showing a relationship between an optical signal Abs and a wavelength according to the present invention.

5 shows an example of constructing a graph of optical signal change according to wavelength according to various sugar concentrations.

The non-invasive biomaterial sugar concentration measuring system 100 of the present invention can show the correlation between the sugar concentration and the light signal change at a specific wavelength by finding out the wavelength of the sensitive region according to the change in sugar concentration.

As shown in FIG. 5, the non-invasive biological material sugar concentration measuring system 100, in the graph expressing the accumulated plurality of optical signal changes in amplitude units, about 580 to 620 nm, which is an amplitude region in which the optical signal change is relatively large, By marking the window, the light signal sensitive area can be distinguished and displayed. The above-exemplified amplitude region around 600 nm is only an example of the invention, and the optical signal sensitive region may change depending on the conditions/circumstances of the sample.

6 is an example of a graph of an optical signal corresponding to a sugar concentration at a highly sensitive wavelength according to the present invention.

The non-invasive biological material glucose concentration measurement system 100 analyzes the optical signal graph corresponding to the sugar concentration as shown in FIG. 6 to implement non-invasive glucose concentration measurement using an optical signal.

In FIG. 6, as the sugar concentration increases, the absorbance (Abs) is represented as a graph in which the absorbance (Abs) gradually increases.

In another example, the non-invasive biomaterial glucose concentration measurement system 100 may analyze the correlation between the sugar concentration and the light signal through MATLAB modeling.

The non-invasive biological material glucose concentration measurement system 100 can be applied to non-blood glucose concentration measurement.

In addition, the non-invasive biomaterial sugar concentration measurement system 100 can be used as an auxiliary means for managing diabetes by developing a user-friendly module so that the general public can track and manage blood sugar levels at home.

In addition, the non-invasive biomaterial sugar concentration measurement system 100 can measure the sugar concentration in a non-invasive manner without loss or damage to the sample.

In addition, since the non-invasive biomaterial sugar concentration measuring system 100 is a non-invasive method, contamination of the sample can be prevented. For example, the non-invasive biological material sugar concentration measurement system 100 may measure the sugar concentration of a liquid sample in a sealed container.

In addition, the non-invasive biological material sugar concentration measuring system 100 can measure the sugar concentration without damaging the solid sample.

In addition, the non-invasive biomaterial sugar concentration measuring system 100 is applied to blood sugar measurement, and it is possible to measure the sugar concentration without the patient's blood collection pain, and it is possible to eliminate the risk of infection to the patient.

In addition, the non-invasive biomaterial glucose concentration measurement system 100 employs an optical non-blood glucose measurement module to replace existing domestic and foreign invasive diabetes measurement devices, thereby increasing economic ripple effect.

In addition, the non-invasive biomaterial sugar concentration measurement system 100 enables long-distance communication and home medical diagnosis through the introduction of the U-Healthcare system, so it is expected to improve the quality of life by providing health management and various health information. .

In addition, the non-invasive biomaterial glucose concentration measurement system 100 is a non-invasive blood glucose analysis device, and has a feature of reducing the pain of blood collection and enabling continuous measurement, so that it can be a reliable blood glucose measurement and ripple medical technology.

In addition, the non-invasive biomaterial glucose concentration measurement system 100 can be commercialized by applying the core technology of optical techniques, and can be used for blood glucose as well as cholesterol analysis.

In addition, the non-invasive biomaterial glucose concentration measurement system 100 may enable various bio-signal analysis and early diagnosis of blood sugar and diseases in a living body.

Hereinafter, in FIG. 7, the workflow of the non-invasive biomaterial glucose concentration measuring system 100 using an optical module according to embodiments of the present invention will be described in detail.

7 is a flowchart illustrating a method for non-invasively measuring a sugar concentration of a biological material using an optical module according to an embodiment of the present invention.

The method of non-invasively measuring the sugar concentration of a biological material using the optical module according to the present embodiment may be performed by the non-invasive biological material sugar concentration measuring system 100 .

First, in the light source in the non-invasive biomaterial sugar concentration measuring system 100, light energy is generated and sent to the sample (710). Step 710 may be a process of emitting light from a light source and outputting it in the form of energy (light energy) as a sample.

The sample is an object for measuring sugar concentration, and may be the skin of a patient whose sugar concentration is measured through conventional blood sampling.

In the first lens in the non-invasive biomaterial sugar concentration measuring system 100, as the light energy reflected by the sample is diffused and converted into reflected light while passing through the slit, the reflected light is converted into parallel light (720). Step 720 may be a process of converting the diffuse reflected light converted by the sample and the slit into collimated light in the first lens.

A slit may be a means of diffusing light through a small hole.

The first lens may be a parallel lens that parallelizes the propagation direction of the light diffused through the slit.

In the diffraction grating in the non-invasive biological material sugar concentration measurement system 100, light for each wavelength is output using parallel light input from the sample (730). Step 730 may be a process of spreading the parallel light by dispersing a wavelength unit in the diffraction grating.

A diffraction grating is a device that separates a spectrum of light according to wavelengths by using a diffraction phenomenon of light, and obtains a spectrum by dividing parallel light passing through a slit according to wavelengths, thereby outputting light according to the wavelengths.

The second lens in the non-invasive biomaterial glucose concentration measuring system 100 reflects the output light for each wavelength to a mirror, and then selects a target specific wavelength among the light for each wavelength (740). Step 740 may play a role of selecting and passing only light of a specific wavelength that is reflected in a predetermined direction by the mirror in the second lens.

The mirror may have a structure that changes the propagation direction of light for a desired wavelength differently from that of other wavelengths.

The second lens may be a filter parallel lens that passes light of a specific wavelength that is reflected by a mirror and reflected in a predetermined traveling direction.

The detector in the non-invasive biomaterial sugar concentration measurement system 100 detects an optical signal of the light of the selected specific wavelength (750). Step 750 may be a process of sensing light of a specific wavelength selected by the second lens in the detector.

The detector may be designed to repeatedly detect only light of a specific wavelength.

The processor in the non-invasive biomaterial sugar concentration measurement system 100 accumulates and stores the sensed optical signal for a predetermined period (760).

In addition, the processor builds a graph of the optical signal change according to the sugar concentration associated with the sample using the accumulated and stored optical signals (770).

Steps 760 and 770 may be processes of accumulating the optical signals detected by the detector according to the arrival of a period in the processor and visualizing the optical signal change for the sample in a graph using the accumulated optical signals.

The processor may determine a sensitive region of the optical signal in the graph of optical signal change according to the sugar concentration, and mark a window in an amplitude range corresponding to the determined sensitive region.

For example, the processor marks a window with an amplitude region in which the optical signal change is relatively large (e.g., about 580 to 620 nm in FIG. can be displayed separately.

In addition, the processor may construct a graph representing a correlation between the sugar concentration and the optical signal as a graph of light signal change according to the sugar concentration.

For example, as a graph representing the correlation, the processor may build a graph in which the absorbance (Abs) gradually increases as the sugar concentration increases. The graph may have a logarithmic function, condition Depending on , it may be a polynomial function, an exponential function, or the like.

According to the present invention, a non-invasive optical technique measures the sugar component concentration of a biological material, increases measurement accuracy based on quantified data, and builds a user-friendly system that can be used by the general public. It is possible to provide an invasive biomaterial sugar concentration measurement system and method.

The embodiments described above may be implemented as hardware components, software components, and/or a combination of hardware components and software components. For example, the devices, methods and components described in the embodiments may include, for example, a processor, a controller, an arithmetic logic unit (ALU), a digital signal processor, a microcomputer, a field programmable gate (FPGA). array), programmable logic units (PLUs), microprocessors, or any other device capable of executing and responding to instructions. The processing device may execute an operating system (OS) and software applications running on the operating system. A processing device may also access, store, manipulate, process, and generate data in response to execution of software. For convenience of understanding, there are cases in which one processing device is used, but those skilled in the art will understand that the processing device includes a plurality of processing elements and/or a plurality of types of processing elements. It can be seen that it can include. For example, a processing device may include a plurality of processors or a processor and a controller. Other processing configurations are also possible, such as parallel processors.

Software may include a computer program, code, instructions, or a combination of one or more of the foregoing, which configures a processing device to operate as desired or processes independently or collectively. The device can be commanded. Software and/or data may be any tangible machine, component, physical device, virtual equipment, computer storage medium or device, intended to be interpreted by or provide instructions or data to a processing device. , or may be permanently or temporarily embodied in a transmitted signal wave. Software may be distributed on networked computer systems and stored or executed in a distributed manner. Software and data may be stored on computer readable media.

The method according to the embodiment may be implemented in the form of program instructions that can be executed through various computer means and recorded on a computer readable medium. A computer readable medium may store program instructions, data files, data structures, etc. alone or in combination, and program instructions recorded on the medium may be specially designed and configured for the embodiment or may be known and usable to those skilled in the art of computer software. there is. Examples of computer-readable recording media include magnetic media such as hard disks, floppy disks and magnetic tapes, optical media such as CD-ROMs and DVDs, and magnetic media such as floptical disks. - includes hardware devices specially configured to store and execute program instructions, such as magneto-optical media, and ROM, RAM, flash memory, and the like. Examples of program instructions include high-level language codes that can be executed by a computer using an interpreter, as well as machine language codes such as those produced by a compiler.

The hardware device described above may be configured to operate as one or a plurality of software modules to perform the operations of the embodiments, and vice versa.

As described above, although the embodiments have been described with limited drawings, those skilled in the art can apply various technical modifications and variations based on this. For example, the described techniques may be performed in an order different from the method described, and/or components of the described system, structure, device, circuit, etc. may be combined or combined in a different form than the method described, or other components may be used. Or even if it is replaced or substituted by equivalents, appropriate results can be achieved.

Therefore, other implementations, other embodiments, and equivalents of the claims are within the scope of the following claims.

Claims (11)

A diffraction grating that outputs light for each wavelength using collimated light input from the sample;
a second lens that reflects the output light for each wavelength to a mirror and then selects light of a specific desired wavelength from among the light for each wavelength;
a detector for detecting an optical signal of the light of the selected specific wavelength; and
A processor for accumulating and storing the sensed light signal for a predetermined period of time, and constructing a graph of light signal change according to sugar concentration associated with the sample using the accumulated light signal.
including,
The processor,
As a graph of the light signal change according to the sugar concentration, a graph in which the absorbance (Abs) increases as the sugar concentration increases,
In the graph, determining a sensitive region of the optical signal and marking a window in an amplitude range corresponding to the determined sensitive region
Non-invasive biomaterial sugar concentration measurement system using an optical module. delete delete delete According to claim 1,
The non-invasive biological material sugar concentration measurement system,
a light source generating light energy and departing from the sample; and
A first lens for converting the reflected light into the collimated light as the light energy reflected by the sample is diffused and converted into reflected light while passing through the slit
Including more,
The diffraction grating,
Dispersing the collimated light according to wavelength to output light for each wavelength
Non-invasive biomaterial sugar concentration measurement system using an optical module. In the diffraction grating, outputting light for each wavelength using parallel light input from the sample;
In a second lens, after reflecting the output light for each wavelength to a mirror, selecting light of a specific target wavelength from among the light for each wavelength;
In a detector, detecting an optical signal of the light of the selected specific wavelength;
accumulating and storing the sensed optical signal for a predetermined period in a processor;
In the processor, constructing a graph of light signal change according to sugar concentration associated with the sample, using the accumulated and stored optical signals, in which absorbance (Abs) increases as the sugar concentration increases;
determining, in the processor, a sensitive region of an optical signal in the graph; and
In the processor, marking a window in an amplitude range corresponding to the determined sensitive region.
Non-invasive biomaterial sugar concentration measurement method using an optical module comprising a. delete delete delete According to claim 6,
In a light source, generating light energy and sending it to the sample; and
In the first lens, as light energy reflected by the sample is diffused while passing through the slit and converted into reflected light, converting the reflected light into the collimated light.
Including more,
In the step of outputting light for each wavelength,
Dispersing the collimated light according to the wavelength to output the light according to the wavelength
Non-invasive biomaterial sugar concentration measurement method using an optical module comprising a. A computer-readable recording medium recording a program for executing the method of claim 6.

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